Switched capacitor defibrillation circuit

ABSTRACT

A defibrillator circuit for generating a rectangular waveform across a patient from capacitively stored energy and employing a plurality of capacitors initially chargeable to a common voltage and thereafter sequentially switchable into parallel relation with one another so as to raise the voltage supplied to an H-bridge circuit from a point of decay back to said common voltage.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of co-pending U.S. application Ser. No. 10/011,952, filed Nov. 5, 2001, the disclosure of which is incorporated herein by reference.

The present invention may find application in systems such as are disclosed in the U.S. patent application entitled “SUBCUTANEOUS ONLY IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR AND OPTIONAL PACER,” having Ser. No. 09/663,607, filed Sep. 18, 2000, now U.S. Pat. No. 6,721,597, and U.S. patent application entitled “UNITARY SUBCUTANEOUS ONLY IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR AND OPTIONAL PACER,” having Ser. No. 09/663,606, filed Sep. 18, 2000, now U.S. Pat. No. 6,647,292, of which both applications are assigned to the assignee of the present application, and the disclosures of both applications are hereby incorporated by reference.

Applications related to the foregoing applications include U.S. application Ser. No. 09/940,283 entitled “DUCKBILL-SHAPED IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR CANISTER AND METHOD OF USE,” U.S. application Ser. No. 09/940,371 entitled “CERAMICS AND/OR OTHER MATERIAL INSULATED SHELL FOR ACTIVE AND NON-ACTIVE S-ICD CAN,” U.S. application Ser. No. 09/940,468 entitled “SUBCUTANEOUS ELECTRODE FOR TRANSTHORACIC CONDUCTION WITH IMPROVED INSTALLATION CHARACTERISTICS,” U.S. application Ser. No. 09/941,814 entitled “SUBCUTANEOUS ELECTRODE WITH IMPROVED CONTACT SHAPE FOR TRANSTHORACIC CONDUCTION,” U.S. application Ser. No. 09/940,356 entitled “SUBCUTANEOUS ELECTRODE FOR TRANSTHORACIC CONDUCTION WITH HIGHLY MANEUVERABLE INSERTION TOOL,” U.S. application Ser. No. 09/940,340 entitled “SUBCUTANEOUS ELECTRODE FOR TRANSTHORACIC CONDUCTION WITH LOW-PROFILE INSTALLATION APPENDAGE AND METHOD OF DOING SAME,” U.S. application Ser. No. 09/940,287 entitled “SUBCUTANEOUS ELECTRODE FOR TRANSTHORACIC CONDUCTION WITH INSERTION TOOL,” U.S. application Ser. No. 09/940,377 entitled “METHOD OF INSERTION AND IMPLANTATION OF IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR CANISTERS,” U.S. application Ser. No. 09/940,599 entitled “CANISTER DESIGNS FOR IMPLANTABLE CARDIOVERTER-DEFIBRILLATORS,” U.S. application Ser. No. 09/940,373 entitled “RADIAN CURVE SHAPED IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR CANISTER,” U.S. application Ser. No. 09/940,273 entitled “CARDIOVERTER-DEFIBRILLATOR HAVING A FOCUSED SHOCKING AREA AND ORIENTATION THEREOF,” U.S. application Ser. No. 09/940,378 entitled “BIPHASIC WAVEFORM FOR ANTI-BRADYCARDIA PACING FOR A SUBCUTANEOUS IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR,” and U.S. application Ser. No. 09/940,266 entitled “BIPHASIC WAVEFORM FOR ANTI-TACHYCARDIA PACING FOR A SUBCUTANEOUS IMPLANTABLE CARDIOVERTER-DEFIBRILLATOR,” the disclosures of which applications are hereby incorporated by reference.

FIELD OF THE INVENTION

The subject invention relates to electronic circuitry and particularly to circuitry having applications in defibrillating apparatus.

BACKGROUND OF THE INVENTION

Defibrillation/cardioversion is a technique employed to counter arrhythmic heart conditions including some tachycardias in the atria and/or ventricles. Typically, electrodes are employed to stimulate the heart with electrical impulses or shocks, of a magnitude substantially greater than pulses used in cardiac pacing. Because current density is a key factor in both defibrillation and pacing, implantable devices may improve what is capable with the standard waveform where the current and voltage decay over the time of pulse deliver. Consequently, a waveform that maintains a constant current over the duration of delivery to the myocardium may improve defibrillation as well as pacing.

Defibrillation/cardioversion systems include body implantable electrodes that are connected to a hermetically sealed container housing the electronics, battery supply and capacitors. The entire system is referred to as an implantable cardioverter/defibrillator (ICD). The electrodes used in ICDs can be in the form of patches applied directly to epicardial tissue, or, more commonly, are on the distal regions of small cylindrical insulated catheters that typically enter the subclavian venous system, pass through the superior vena cava and, into one or more endocardial areas of the heart. Such electrode systems are called intravascular or transvenous electrodes. U.S. Pat. Nos. 4,603,705, 4,693,253; 4,944,300; and 5,105,810, the disclosures of which are all incorporated herein by reference, disclose intravascular or transvenous electrodes, employed either alone, in combination with other intravascular or transvenous electrodes, or in combination with an epicardial patch or subcutaneous electrodes. Compliant epicardial defibrillator electrodes are disclosed in U.S. Pat. Nos. 4,567,900 and 5,618,287, the disclosures of which are incorporated herein by reference. A sensing epicardial electrode configuration is disclosed in U.S. Pat No. 5,476,503, the disclosure of which is incorporated herein by reference.

In addition to epicardial and transvenous electrodes, subcutaneous electrode systems have also been developed. For example, U.S. Pat. Nos. 5,342,407 and 5,603,732, the disclosures of which are incorporated herein by reference, teach the use of a pulse monitor/generator surgically implanted into the abdomen and subcutaneous electrodes implanted in the thorax. This system is far more complicated to use than current ICD systems using transvenous lead systems together with an active can electrode, and therefore, it has no practical use. It has, in fact, never been used because of the surgical difficulty of applying such a device (3 incisions), the impractical abdominal location of the generator and the electrically poor sensing and defibrillation aspects of such a system.

Recent efforts to improve the efficiency of ICDs have led manufacturers to produce ICDs which are small enough to be implanted in the pectoral region. In addition, advances in circuit design have enabled the housing of the ICD to form a subcutaneous electrode. Some examples of ICDs in which the housing of the ICD serves as an optional additional electrode are described in U.S. Pat. Nos. 5,133,353; 5,261,400; 5,620,477; and 5,658,321, the disclosures of which are incorporated herein by reference.

ICDs are now an established therapy for the management of life threatening cardiac rhythm disorders, primarily ventricular fibrillation (V-Fib). ICDs are very effective at treating V-Fib, but are therapies that still require significant surgery.

As ICD therapy becomes more prophylactic in nature and used in progressively less ill individuals, especially children at risk of cardiac arrest, the requirement of ICD therapy to use intravenous catheters and transvenous leads is an impediment to very long term management as most individuals will begin to develop complications related to lead system malfunction sometime in the 5- to 10-year time frame, often earlier. In addition, chronic transvenous lead systems, their reimplantation and removals, can damage major cardiovascular venous systems and the tricuspid valve, as well as result in life threatening perforations of the great vessels and heart. Consequently, use of transvenous lead systems, despite their many advantages, are not without their chronic patient management limitations in those with life expectancies of ≦5 years. The problem of lead complications is even greater in children where body growth can substantially alter transvenous lead function and lead to additional cardiovascular problems and revisions. Moreover, transvenous ICD systems also increase cost and require specialized interventional rooms and equipment as well as special skill for insertion. These systems are typically implanted by cardiac electrophysiologists who have had a great deal of extra training.

In addition to the background related to ICD therapy, the present invention requires a brief understanding of a related therapy, the automatic external defibrillator (AED). AEDs employ the use of cutaneous patch electrodes, rather than implantable lead systems, to effect defibrillation under the direction of a bystander user who treats the patient suffering from V-Fib with a portable device containing the necessary electronics and power supply that allows defibrillation. AEDs can be nearly as effective as an ICD for defibrillation if applied to the victim of ventricular fibrillation promptly, i.e., within 2 to 3 minutes of the onset of the ventricular fibrillation.

AED therapy has great appeal as a tool for diminishing the risk of death in public venues such as in air flight. However, an AED must be used by another individual, not the person suffering from the potential fatal rhythm. It is more of a public health tool than a patient-specific tool like an ICD. Because >75% of cardiac arrests occur in the home, and over half occur in the bedroom, patients at risk of cardiac arrest are often alone or asleep and cannot be helped in time with an AED. Moreover, its success depends to a reasonable degree on an acceptable level of skill and calm by the bystander user.

What is needed therefore, especially for children and for prophylactic long term use for those at risk of cardiac arrest, is a combination of the two forms of therapy which would provide prompt and near-certain defibrillation, like an ICD, but without the long-term adverse sequelae of a transvenous lead system while simultaneously using most of the simpler and lower cost technology of an AED. What is also needed is a cardioverter/defibrillator that is of simple design and can be comfortably implanted in a patient for many years.

Moreover, it has appeared advantageous to the inventor to provide the capability in such improved circuitry to produce a defibrillating waveform which includes a defibrillating pulse approximating a rectangular pulse. Such a pulse is advantageous, for example, because it can approximate a constant current density across the heart.

SUMMARY

According to the invention, circuitry is provided for enabling the generation of an approximation of a rectangular waveform from energy stored in energy storage devices such as a capacitor.

BRIEF DESCRIPTION OF THE DRAWINGS

For a better understanding of the invention, reference is now made to the drawings where like numerals represent similar objects throughout the figures and wherein:

FIG. 1 is an electrical circuit schematic of an illustrative embodiment of the invention;

FIG. 2 is a waveform diagram illustrative of operation of the circuit of FIG. 1; and

FIG. 3 is a waveform diagram illustrative of operation of the circuit of FIG. 1.

DETAILED DESCRIPTION OF ILLUSTRATIVE EMBODIMENTS

An illustrative embodiment is shown in FIG. 1. The illustrative embodiment includes an H bridge circuit 13 and a drive circuit 15 for supplying voltage or energy to the H bridge circuit 13.

The H bridge circuit 13 may be of conventional form, including first and second high side switches H₁, H₂ and first and second low side switches L₁, L₂. The switches H₁, H₂; L₁, L₂ may be manipulated to appropriately and selectively apply a voltage present at junction 17 across a patient indicated by a patient resistance R_(PAT). The H bridge circuit 13 may also include features disclosed in co-pending application Ser. Nos. 10/011,955 and 10/011,957, filed herewith on behalf of inventor Alan H. Ostroff and entitled Defibrillation Pacing Circuitry and Simplified Defibrillator Output Circuit.

The drive circuit 15 of FIG. 1 includes a plurality of energy storage devices in the illustrative form of four capacitors C₁, C₂, C₃, C₄. Across each capacitor Cl, C₂, C₃, C₄ is connected a respective secondary l₁, l₂, l₃, l₄ of a transformer T₁. The primary of the transformer T₁ is switchable via a switch SW₁ to connect to a source of D.C. voltage V_(S), e.g., a battery.

The first capacitor C₁ has a first terminal connected to ground and a second terminal in common with the junction 17. The second terminal of the capacitor C₁ is further connected to the cathode of a diode D₁, whose anode is connected to a first terminal of the first secondary winding l₁. The remaining capacitors C₂, C₃, C₄ have second terminals which are switchable via respective switches SW₂, SW₃, SW₄ to establish or remove electrical connection to the junction 17. The respective first terminals of the capacitors C₂, C₃, C₄ are connected to respective switches SW₅, SW₆, SW₇ which can be selectively operated to connect those respective first terminals to ground. The respective second terminals of the capacitors C₂, C₃, C₄ are connected to the respective cathodes of respective diodes D₂, D₃, D₄. The respective anodes of the diodes D₂, D₃, D₄ are connected to respective first terminals of the secondary windings l₂, l₃, l₄, whose second terminals are connected to ground.

In illustrative operation of the circuit of FIG. 1, the capacitors C₁, C₂, C₃, C₄ are charged to a common voltage level V. Next, the high side switch H₁ and the low side switch L₂ are closed while H₂ and L₁ are open, thereby connecting the voltage on the capacitor C₁ across the patient resistance R_(PAT).

As shown in FIG. 2, the voltage across the patient is initially V_(PAT) and decays with a time constant RC₁ for a selected time period up to a point in time denoted t₁ in FIG. 2. At time t₁, a switching signal Φ₂ (FIG. 3) is activated to close the switch SW₂. The patient voltage V_(PAT) initially rises and then begins to decay with a time constant equal to R(C₁+C₂). At a selected time t₂, a switching signal Φ₃ is activated, closing the switch SW₃ and connecting the voltage across the capacitor C₃ to the junction 17. As shown in FIG. 2, the patient voltage again rises and thereafter begins to decay with a time constant equal to R(C₁+C₂+C₃). Then, at time t₃, the switching signal Φ₄ is activated, closing the switch SW₄, thereby applying the voltage across the capacitor C₄ and to the junction 17, again resulting in the voltage V_(PAT) rising and thereafter decaying with a time constant R(C₁+C₂+C₃+C₄). Finally, at time t₄, the switches H₁, L₂ are opened, thereby terminating the first phase of the waveform.

If desired, these switches H₂, L₁ may then be closed to produce a conventional second phase 19 of a biphasic waveform. This waveform drops to a voltage V_(PAT1) and then decays with a time constant determined by the patient resistance R_(PAT) and the effective value of the parallel capacitors C₁, C₂, C₃, C₄. An inverted biphasic waveform may also be produced by first activating H₂ and L₁.

It will be observed that circuitry according to the preferred embodiment produces an approximation to a square or rectangular pulse. The times t₁, t₂, t₃, t₄ can easily be adjusted to further control the shape of the waveform, for example, such that ΔV remains constant for each interval of decay despite the change in time constants each time an additional capacitor, e.g., C₂, C₃, C₄, is switched into the current. Additionally, the number of parallel capacitors, e.g., C₁, C₂, C₃, etc., may be more or less than the number depicted in FIG. 1, a particularly useful range being two to seven.

While the present invention has been described above in terms of specific embodiments, it is to be understood that the invention is not limited to the disclosed embodiments. On the contrary, the following claims are intended to cover various modifications and equivalent methods and structures included within the spirit and scope of the invention. 

1. A device for providing electrical cardiac treatment, the device comprising: first capacitor means for storing and discharging electrical energy; second capacitor means for storing and discharging electrical energy; and a first switch coupled to the first capacitor means and second capacitor means such that: when the first switch is in a first state, the second capacitor means is isolated from the first capacitor means; and when the first switch is in a second state, the second capacitor means is connected in parallel to the first capacitor means.
 2. The device of claim 1, further comprising an H-bridge output circuit for delivering energy from the capacitor means to a receiver for receiving the proximal end of a lead electrode assembly.
 3. The device of claim 2, further comprising a control circuit coupled to the switch and the H-bridge, the control circuit adapted to provide control signals causing the H-bridge to send a biphasic waveform to the lead, the control circuit further adapted to cause the switch to be: in the first state for a first portion of the first phase of the biphasic waveform; and in the second state for a second portion of the first phase of the biphasic waveform.
 4. The device of claim 3, wherein the control circuit is also adapted to cause the switch to be in the second state during the second phase of the biphasic waveform.
 5. The device of claim 1, wherein the capacitor means are housed in a canister and the device is adapted to provide the electric signal between an electrode disposed on the canister and a receiver for receiving the proximal end of a lead electrode assembly.
 6. The device of claim 1, wherein the capacitor means are housed in a canister and the device is adapted to provide the electric signal between two electrodes disposed on a lead electrode assembly secured to the canister.
 7. A device for providing electrical cardiac treatment, the device comprising: a plurality of separate energy storage devices each characterized by a degrading discharge curve; at least one switch coupled to the plurality of energy storage devices such that: when a switch is in a first state it causes a first energy storage device to be isolated from a second energy storage device; and when the switch is in a second state it causes the first energy storage device to be connected in parallel to the second energy storage device; and a control circuit coupled to the at least one switch and adapted to enable the first energy storage device to be sequentially coupled in parallel to additional energy storage devices.
 8. The device of claim 7, wherein the at least one energy storage device includes at least one capacitor.
 9. The device of claim 7, further comprising an H-bridge output circuit for delivering energy from the at least one energy storage device to a receiver for receiving the proximal end of a lead electrode assembly.
 10. The device of claim 9, wherein the control circuit is coupled to the H-bridge and is adapted to provide control signals causing the H-bridge to send a biphasic waveform to receiver for the lead electrode assembly.
 11. The device of claim 10, wherein the control circuit is also adapted to cause the at least one switch to sequentially place each of the plurality of energy storage devices in parallel during the second phase of the biphasic waveform.
 12. The device of claim 7, wherein the at least one energy storage device is housed in a canister and the electric signal is provided between the canister and a receiver for receiving the proximal end of a lead electrode assembly.
 13. The device of claim 7, wherein the device is adapted to provide the electric signal between two electrodes disposed on a lead electrode assembly.
 14. A device for providing electrical cardiac treatment, the device comprising: a first capacitor; means for selectively coupling the first capacitor to a lead electrode assembly; a second capacitor; and a first switch coupled to the first and second capacitors such that, when the means for selectively coupling the first capacitor to the lead is enabled to couple the first capacitor to the lead: when the switch is in a first state, the second capacitor is isolated from the first capacitor; and when the switch is in a second state, the second capacitor is connected in parallel to the first capacitor.
 15. The device of claim 14, wherein the means for selectively coupling includes an H-bridge circuit.
 16. The device of claim 14, further comprising a control circuit coupled to the switch and the means for selectively coupling, the control circuit adapted to provide control signals causing the means for selectively coupling to provide a biphasic waveform to the lead, the control circuit further adapted to cause the switch to be: in the first state for a first portion of the first phase of the biphasic waveform; and in the second state for a second portion of the first phase of the biphasic waveform.
 17. The device of claim 16, wherein the control circuit is also adapted to cause the switch to be in the second state during the second phase of the biphasic waveform.
 18. The device of claim 14, further comprising a canister.
 19. The device of claim 18, wherein the capacitors are housed in the canister and the device is adapted to selectively provide an electric stimulus between the lead electrode assembly and an electrode disposed on the canister.
 20. The device of claim 18, wherein the device is adapted to provide the electric signal between two electrodes disposed on the lead electrode assembly. 